Active transmit elements for MRI coils and other antenna devices, and method

ABSTRACT

Apparatus and method that includes amplifiers for transceiver antenna elements, and more specifically to power amplifying an RF (radio frequency) signal using a distributed power amplifier having electronic devices (such as field-effect transistors) that are thermally and/or mechanically connected to each one of a plurality of antenna elements (also called coil elements) to form a hybrid coil-amplifier (e.g., for use in a magnetic-resonance (MR) imaging or spectroscopy machine), and that is optionally adjusted from a remote location, optionally including remotely adjusting its gains, electrical resistances, inductances, and/or capacitances (which controls the magnitude, phase, frequency, spatial profile, and temporal profile of the RF signal)—and, in some embodiments, the components are compatible with, and function in, high fields (such as a magnetic field of up to and exceeding one tesla or even ten tesla or more and/or an electric field of many thousands of volts per meter).

RELATED APPLICATION

This application is a divisional of U.S. patent application Ser. No.12/879,000 filed Sep. 9, 2010, titled “Active transmit elements for MRIcoils and other antenna devices” (to issue as U.S. Pat. No. 8,604,791 onDec. 10, 2013), which is incorporated herein by reference in itsentirety.

FIELD OF THE INVENTION

This invention relates to the field of amplifiers for transceiverantenna elements, and more specifically to a method and apparatus forpower amplifying an RF (radio frequency) signal using a distributedpower amplifier having electronic devices (such as field-effecttransistors) that are thermally and/or mechanically connected to eachone of a plurality of antenna elements (also called coil elements) toform a hybrid coil-amplifier (e.g., for use in a magnetic-resonance (MR)imaging or spectroscopy machine), and that is optionally adjusted from aremote location, optionally including remotely adjusting its gains,electrical resistances, inductances, and/or capacitances (which controlsthe magnitude, phase, frequency, spatial profile, and temporal profileof the RF signal)—and, in some embodiments, the components arecompatible with, and function in, high fields (such as a magnetic fieldof up to and exceeding one tesla or even ten tesla or more and/or anelectric field of many thousands of volts per meter).

BACKGROUND OF THE INVENTION

Conventional magnetic-resonance (MR) machines (such as MR imaging (MRI)machines or MR spectroscopy (MRS) machines) employ a high-field-strengthmagnet (e.g., a superconducting-coil magnet having a constant (DC)magnetic field of about one tesla (1 T) or more, as well as a gradientmagnet coil (which generates an additional magnetic field whose strengthvaries over space in a desired manner), and a radio-frequency (RF)transmit-and-receive coil device (RF-coil device) that includes aplurality of transmit-antenna elements and a plurality ofreceive-antenna elements. RF signal generators and RF power amplifiersare conventionally located in a control room remote from the RF-coildevices, and the RF power amplifiers have their output signals combinedand then coupled to the RF-coil device via high-power-capabilitywell-shielded coaxial cables (frequently called just “coax”). Suchconventional designs typically use a plurality of medium-high poweramplifiers (e.g., in some conventional circuits, each such medium-highpower amplifiers is capable of outputting 500 W to 5000 W) together toamplify an RF signal, thus generating a plurality of medium-high-powerRF signals (e.g., wherein the total RF power of this plurality ofsignals may be as high as 50 kW), and these are combined (using acombiner circuit that often incurs losses of up to 50% or more of thesignal) to form a single very-high-power signal (of perhaps 30 kW, dueto losses taken from the 50 kW in the plurality of medium-power signals)and then transmitted (using coaxial cables that typically incuradditional losses of up to 50% or more of the signal by the time thesignal is coupled to the RF-coil device in the MR magnet bore (theopening through the center of the DC magnet)). Because of the high powerof the RF transmit signal, it is infeasible to wirelessly couple it fromthe remote control-room power amplifiers to the RF-coil device in the MRmagnet bore.

U.S. patent application Ser. No. 12/719,841 titled “REMOTELY ADJUSTABLEREACTIVE AND RESISTIVE ELECTRICAL ELEMENTS AND METHOD” filed 8 Mar. 2010by Carl Snyder et al. (which issued as U.S. Pat. No. 8,299,681 on Oct.30, 2012) is incorporated herein by reference. Snyder et al. describe anapparatus and method that include providing a variable-parameterelectrical component in a high-field environment and based on anelectrical signal, automatically moving a movable portion of theelectrical component in relation to another portion of the electricalcomponent to vary at least one of its parameters. In some embodiments,the moving uses a mechanical movement device (e.g., a linear positioner,rotary motor, or pump). In some embodiments of the method, theelectrical component has a variable inductance, capacitance, and/orresistance. Some embodiments include using a computer that controls themoving of the movable portion of the electrical component in order tovary an electrical parameter of the electrical component. Someembodiments include using a feedback signal to provide feedback controlin order to adjust and/or maintain the electrical parameter. Someembodiments include a non-magnetic positioner connected to an electricalcomponent configured to have its RLC parameters varied by thepositioner.

The basis of MRI is the directional magnetic field, or moment,associated with charged particles in motion. Nuclei containing an oddnumber of protons and/or neutrons have a characteristic motion orprecession. Because nuclei are charged particles, this precessionproduces a small magnetic moment. When a human body is placed in a largemagnetic field, many of the free hydrogen nuclei align themselves withthe direction of the magnetic field. The nuclei precess about themagnetic field direction like gyroscopes. This behavior is termed Larmorprecession. The frequency of Larmor precession is proportional to theapplied magnetic field strength as defined by the Larmor frequency,ω₀=γB₀, where γ is the gyromagnetic ratio and B₀ is the strength of theapplied magnetic field. The gyromagnetic ratio is a nuclei specificconstant. For hydrogen, γ=42.5 MHz/Tesla. To obtain an MR image of anobject, the object is placed in a uniform high-strength magnetic field,of between 0.5 to 1.5 Tesla. As a result, the object's hydrogen nucleialign with the magnetic field B₀ and create a net magnetic moment M₀parallel to B₀. Next, a radio-frequency (RF) pulse, B_(rf), is appliedperpendicular to B₀. This pulse, with a frequency equal to the Larmorfrequency, causes M to tilt away from B₀. Once the RF signal is removed,the nuclei realign themselves such that their net magnetic moment, M, isagain parallel with B₀. This return to equilibrium is referred to asrelaxation. During relaxation, the nuclei lose energy by emitting theirown RF signal. This signal is referred to as the free-induction decay(FID) response signal. The FID response signal is measured by aconductive field coil placed around the object being imaged. Thismeasurement is processed or reconstructed to obtain 3D MR images. (Thisparagraph is by Blair Mackiewich, Masters thesis, 1995)

For example, approximately 64 MHz is used for MRI machines having1.5-Tesla magnets (these are used for most MR machine platforms in theworld today), 128 MHz is used for MRI machines having 3-T magnets(currently the fastest-growing segment of the MR market), 300 MHz isused for MRI machines having 7-T magnets (considered the highest-fieldmachines supported by industry today), 400 MHz is used for MRI machineshaving 9.4-T magnets (it is believed there are now only three in use inthe world), and 450 MHz is used for the MRI machine having a 10.5-Tmagnet (currently, just the Center for Magnetic Resonance Research(CMRR) at the University of Minnesota operates one of these).

U.S. Pat. No. 4,682,125 to Harrison et al. issued Jul. 21, 1987 titled“RF coil coupling for MRI with tuned RF rejection circuit using coaxshield choke” is incorporated herein by reference in its entirety forall purposes. Harrison et al. describe undesirable RF coupling via theoutside of an outer coaxial cable conductor to/from RF coils in amagnetic resonance imaging apparatus is minimized by employing aparallel resonance tuned RF choke in the circuit. The choke is realizedby forming a short coiled section of the coaxial cable with a lumpedfixed capacitance connected in parallel thereacross and a conductivetuning rod positioned within the center of the coiled section so as totrim the parallel resonant frequency to the desired value.

U.S. Pat. No. 4,763,076 to Arakawa et al. issued Aug. 9, 1988 titled“MRI transmit coil disable switching via RF in/out cable” isincorporated herein by reference in its entirety for all purposes, anddescribes a detuning/decoupling arrangement for a Magnetic ResonanceImaging (MRI) system RF coil arrangement (of the typing using thenuclear magnetic resonance (NMR) phenomenon) that uses switching diodesto selectively connect and disconnect portions of an RF resonant circuitin response to a DC control signal. The DC control signal selectivelyforward biases and reverse biases the switching diodes. The DC controlcurrent is fed to the resonant circuit along the same RF transmissionline used to feed RF signals to/from the circuit. An in-line coaxialshielded RF choke connected to the RF transmission line isolates the DCcontrol signals from the RF signals flowing on the same transmissionline—reducing the number and complexity of isolation devices required onthe ends of the transmission line to separate the RF and DC signals.

Conventional MR machines and their components and operation aredescribed in numerous patents and patent application such as U.S. Pat.No. 4,947,119 to Ugurbil et al., U.S. Pat. No. 5,908,386 to Ugurbil etal., U.S. Pat. No. 6,650,116 to Garwood et al., U.S. Pat. No. 6,788,056to Vaughan et al., U.S. Pat. No. 6,788,057 to Petropoulos et al., U.S.Pat. No. 6,788,058 to Petropoulos et al., U.S. Pat. No. 6,930,480 toFijita et al., U.S. Pat. No. 6,946,840 to Zou et al., U.S. Pat. No.6,958,607 to Vaughan et al., U.S. Pat. No. 6,969,992 to Vaughan et al.,U.S. Pat. No. 6,975,115 to Fujita et al., U.S. Pat. No. 6,977,502 toHertz, U.S. Pat. No. 6,980,002 to Petropoulos et al., U.S. Pat. No.7,042,222 to Zheng et al., U.S. Pat. No. 7,084,631 to Qu et al., U.S.Pat. No. 7,279,899 to Michaeli et al., U.S. Pat. No. 7,403,006 toGarwood et al., U.S. Pat. No. 7,514,926 to Vaughan et al., U.S. Pat. No.7,598,739 to Vaughan et al., U.S. Pat. No. 7,633,293 to Olson et al.,U.S. Pat. No. 7,710,117 to Vaughan et al., U.S. Patent Publication 2004027128A1 to Vaughan et al., U.S. Patent Publication 2006 001426A1 toVaughan et al., U.S. Patent Publication 2008 0084210A1 to Vaughan etal., U.S. Patent Publication 2008 0129298A1 Vaughan et al., U.S. PatentPublication 2009 115417A1 to Akgun et al., U.S. Patent Publication 2009237077A1 to Vaughan et al., and U.S. Patent Publication 2009 0264733A1to Corum et al.; all of which are incorporated herein by reference intheir entirety for all purposes.

U.S. Pat. No. 4,947,119 to Ugurbil et al. (incorporated herein byreference in its entirety for all purposes) describes several magneticresonance imaging (MRI) methods using adiabatic excitation. One methodaccomplishes slice selection with gradient-modulated adiabaticexcitation. Another method employs slice selection with adiabaticexcitation despite large variations in B₁ magnitude. There is alsodescribed ₁H spectroscopy using solvent suppressive adiabatic pulses.

U.S. Pat. No. 5,908,386 to Ugurbil et al. (incorporated herein byreference in its entirety for all purposes) describes contrastpreparation based on Modified Driven Equilibrium Fourier Transfer andgenerates T1 weighted images for assessment of the myocardial perfusionwith contrast agent first-pass kinetics. The preparation scheme producesT1 contrast with insensitivity to arrhythmias in prospectively triggeredsequential imaging.

U.S. Pat. No. 6,650,116 to Garwood et al. (incorporated herein byreference in its entirety for all purposes) describes performing MRI andNMR spectroscopy that improves the dynamic range of the received signalby using adiabatic RF pulses for spin excitation rather than for spininversion. The preferred adiabatic RF excitation produces a spatiallyvarying phase across the slab, and a sharp slab profile. The phasevariation is divided up by a phase-encoding gradient into voxels havinga phase variation that is negligible over the width of the voxel. Thephase variation in the slab-select direction is, on the whole, largeenough that the peak amplitude of the received signal is reduced and thesignal width broadened.

U.S. Pat. No. 6,788,056 to Vaughan et al. (incorporated herein byreference in its entirety for all purposes) describes an apparatus witha radio frequency magnetic field unit to generate a desired magneticfield. In one embodiment, the radio frequency magnetic field unitincludes a first aperture that is substantially unobstructed and asecond aperture contiguous to the first aperture. In an alternativeembodiment, the radio frequency magnetic field unit includes a firstside aperture, a second side aperture and one or more end apertures. Inone embodiment, a current element is removed from a radio frequencymagnetic field unit to form a magnetic field unit having an aperture. Inan alternative embodiment, two current elements located opposite fromone another in a radio frequency magnetic field unit are removed to forma magnetic filed unit having a first side aperture and a second sideaperture.

U.S. Pat. No. 6,788,057 to Petropoulos et al. (incorporated herein byreference in its entirety for all purposes) describes an MRI gradientcoil set that includes a uniplanar Z-gradient coil, a biplanarX-gradient coil, and a biplanar Y-gradient coil. The coil set providesan open Z-axis face.

U.S. Pat. No. 6,788,058 to Petropoulos et al. (incorporated herein byreference in its entirety for all purposes) describes an MRI coil havingan axis and a first end and an opposite second end with respect to saidaxis includes a first ring element at the first end, a second ringelement, a third ring element, a fourth ring element at the second endwhere the first ring element encompasses a smaller area than each of thesecond, third, and fourth ring elements. The coil also includes aplurality of axial elements connected between the first, second, thirdand fourth ring elements. The third and fourth ring elements are axiallycloser than the first and second ring elements.

U.S. Pat. No. 6,930,480 to Fijita et al. (incorporated herein byreference in its entirety for all purposes) describes a partiallyparallel acquisition RF coil array for imaging a human head includes atleast a first, a second and a third loop coil adapted to be arrangedcircumambiently about the lower portion of the head; and at least aforth, a fifth and a sixth coil adapted to be conformably arranged aboutthe summit of the head. A partially parallel acquisition RF coil arrayfor imaging a human head includes at least a first, a second, a thirdand a fourth loop coil adapted to be arranged circumambiently about thelower portion of the head; and at least a first and a secondfigure-eight or saddle coil adapted to be conformably arranged about thesummit of the head.

U.S. Pat. No. 6,946,840 to Zou et al. (incorporated herein by referencein its entirety for all purposes) describes an MRI array coil includes aplurality of first coils in a receive coil array and a plurality ofsecond coils in a transmit coil array. The receive coil array and thetransmit coil array are electrically disjoint.

U.S. Pat. No. 6,958,607 to Vaughan et al. (incorporated herein byreference in its entirety for all purposes) describes a radio frequencymagnetic field unit to generate a desired magnetic field. In oneembodiment, the RF magnetic field unit includes a first aperture that issubstantially unobstructed and a second aperture contiguous to the firstaperture. In an alternative embodiment, the RF magnetic field unitincludes a first side aperture, a second side aperture and one or moreend apertures. In one embodiment, a current element is removed from a RFmagnetic field unit to form a magnetic field unit having an aperture. Inan alternative embodiment, two current elements located opposite fromone another in a RF magnetic field unit are removed to form a magneticfield unit having a first side aperture and a second side aperture.

U.S. Pat. No. 6,969,992 to Vaughan et al. (incorporated herein byreference in its entirety for all purposes) describes an excitation anddetection circuit having individually controllable elements for use witha multi-element RF coil. Characteristics of the driving signal,including, for example, the phase, amplitude, frequency and timing, fromeach element of the circuit is separately controllable using smallsignals. Negative feedback for the driving signal associated with eachcoil element is derived from a receiver coupled to that coil element.

U.S. Pat. No. 6,975,115 to Fujita et al. (incorporated herein byreference in its entirety for all purposes) describes a partiallyparallel acquisition RF coil array for imaging a sample includes atleast a first, a second and a third coil adapted to be arrangedcircumambiently about the sample and to provide both contrast data andspatial-phase-encoding data.

U.S. Pat. No. 6,977,502 to Hertz (incorporated herein by reference inits entirety for all purposes) describes a configurable matrix receivercomprises a plurality of antennas that detect one or more signals. Theantennas are coupled to a configurable matrix comprising a plurality ofamplifiers, one or more switches that selectively couple the amplifiersin series fashion, and one or more analog-to-digital converters (ADCs)that convert the output signals generated by the amplifiers to digitalform. For example, in one embodiment, a matrix comprises a firstamplifier having a first input and a first output, and a secondamplifier having a second input and a second output, a switch to couplethe first output of the first amplifier to a the second input of thesecond amplifier, a first ADC coupled to the first output of the firstamplifier, and a second ADC coupled to the second output of the secondamplifier. In one embodiment, the signals detected by the antennasinclude magnetic resonance (MR) signals.

U.S. Pat. No. 6,980,002 to Petropoulos et al. (incorporated herein byreference in its entirety for all purposes) describes an MRI array coilfor imaging a human includes a posterior array, an anterior torso arrayand an anterior head-neck-upper-chest array. The head-neck-upper-chestarray has a head portion mountable to the anterior array and aneck-upper-chest portion hingingly attached to the head portion.

U.S. Pat. No. 7,042,222 to Zheng et al. (incorporated herein byreference in its entirety for all purposes) describes a phased-arrayknee coil that includes a transmit coil array and a receive coil arrayhaving a plurality of coils configured to provide a first imaging modeand a second imaging mode.

U.S. Pat. No. 7,084,631 to Qu et al. (incorporated herein by referencein its entirety for all purposes) describes an MRI array coil system andmethod for breast imaging. The MRI array coil system includes a top coilportion with two openings configured to receive therethrough objects tobe imaged. The MRI array coil system further includes a bottom coilportion having two openings configured to access from sides of thebottom coil portion the objects to be imaged. The top coil portion andbottom coil portion each have a plurality of coil elements configured toprovide parallel imaging.

U.S. Pat. No. 7,279,899 to Michaeli et al. (incorporated herein byreference in its entirety for all purposes) describes modulatingtransverse and longitudinal relaxation time contrast in a rotating framebased on a train of RF pulses.

U.S. Pat. No. 7,403,006 to Garwood et al. (incorporated herein byreference in its entirety for all purposes) describes magnetic resonancethat uses a frequency-swept excitation wherein the acquired signal is atime domain signal is provided. In one embodiment, the sweepingfrequency excitation has a duration and is configured to sequentiallyexcite isochromats having different resonant frequencies. Acquisition ofthe time domain signal is done during the duration of the sweepingfrequency excitation. The time domain signal is based on evolution ofthe isochromats.

U.S. Pat. No. 7,514,926 to Adriany et al. (incorporated herein byreference in its entirety for all purposes) describes a coil having aplurality of resonant elements and an adjustable frame. A position of atleast one resonant element can be adjusted relative to at least oneother resonant element. A variable impedance is coupled to adjacentresonant elements and the impedance varies as a function of a separationdistance. Cables are coupled to each resonant element and are gatheredat a junction in a particular manner.

U.S. Pat. No. 7,598,739 to Vaughan et al. (incorporated herein byreference in its entirety for all purposes) describes a plurality oflinear current elements configured about a specimen to be imaged. Acurrent in each current element is controlled independent of a currentin other current elements to select a gradient and to provide radiofrequency shimming. Each current element is driven by a separate channelof a transmitter and connected to a separate channel of a multi-channelreceiver. The impedance, and therefore, the current, in each currentelement is controlled mechanically or electrically.

U.S. Pat. No. 7,633,293 to Olson et al. (incorporated herein byreference in its entirety for all purposes) describes technology forcontrolling non-uniformity in the B₁ field includes selecting the phase,magnitude, frequency, time, or spatial relationship among variouselements of a multi-channel excitation coil in order to control theradio frequency (RF) power emanating from the coil antenna elements.Non-uniformity can be used to steer a constructively interfering B₁field node to spatially correlate with an anatomic region of interest. Aconvex (quadratically constrained quadratic problem) formulation of theB₁ localization problem can be used to select parameters for excitingthe coil. Localization can be used in simulated Finite Difference TimeDomain B₁ field human-head distributions and human-head-phantommeasurement.

U.S. Pat. No. 7,710,117 to Vaughan et al. (incorporated herein byreference in its entirety for all purposes) describes a current unithaving two or more current paths that allows control of magnitude,phase, time, frequency and position of each of element in a radiofrequency coil. For each current element, the current can be adjusted asto a phase angle, frequency and magnitude. Multiple current paths of acurrent unit can be used for targeting multiple spatial domains orstrategic combinations of the fields generated/detected by combinationof elements for targeting a single domain in magnitude, phase, time,space and frequency.

U.S. Patent Publication 2008 0129298A1 to Vaughan et al. (incorporatedherein by reference in its entirety for all purposes) describesmulti-channel magnetic resonance using a TEM coil.

U.S. Patent Publication 2009 0115417A1 to Akgun et al. (incorporatedherein by reference in its entirety for all purposes) describes an RFhaving a plurality of transmission line elements, wherein at least oneof the plurality of transmission line elements may have at least onedimension different than a dimension of another one of the plurality oftransmission line elements. In some cases, each of the transmission lineelements may include a signal line conductor and a ground planeconductor separated by a dielectric.

U.S. Patent Publication 2009 0237077A1 to Vaughan et al. (incorporatedherein by reference in its entirety for all purposes) describes an RFcoil system for MR applications that includes a multi-channel RF coiltransceiver and a multi-channel RF coil. The RF coil system isstructured for reconfiguration between a plurality of operational modes.

U.S. Patent Publication 2009 0264733A1 to Corum et al. (incorporatedherein by reference in its entirety for all purposes) describes apositive contrast MRI feature using a high transverse relaxation ratecontrast agent.

U.S. Pat. No. 6,495,069 issued Dec. 17, 2002 to Lussey et al. titled“Polymer composition,” is incorporated herein by reference. Lussey etal. describe a polymer composition comprises at least one substantiallynon-conductive polymer and at least one electrically conductive fillerand in the form of granules. Their elastomer material was proposed fordevices for controlling or switching electric current, to avoid or limitdisadvantages such as the generation of transients and sparks which areassociated with the actuation of conventional mechanical switches. Theydescribed an electrical conductor composite providing conduction whensubjected to mechanical stress or electrostatic charge but electricallyinsulating when quiescent comprising a granular composition each granuleof which comprises at least one substantially non-conductive polymer andat least one electrically conductive filler and is electricallyinsulating when quiescent but conductive when subjected to mechanicalstress. They did not propose a means for electrically activating suchswitches.

U.S. Pat. No. 7,672,650 to Sorrells et al. issued Mar. 2, 2010 titled“Systems and methods of RF power transmission, modulation, andamplification, including multiple input single output (MISO) amplifierembodiments comprising harmonic control circuitry” and is incorporatedherein by reference. Sonells et al. describe methods and systems forvector combining power amplification. In one embodiment, signals areindividually amplified, then summed to form a desired time-varyingcomplex envelope signal. Phase and/or frequency characteristics of oneor more of the signals are controlled to provide the desired phase,frequency, and/or amplitude characteristics of the desired time-varyingcomplex envelope signal. In another embodiment, a time-varying complexenvelope signal is decomposed into a plurality of constant envelopeconstituent signals. The constituent signals are amplified equally orsubstantially equally, and then summed to construct an amplified versionof the original time-varying envelope signal. Embodiments also performfrequency up-conversion. However, neither operation in high fields noroperation where the control of the circuit is distal from the RFantennae, are discussed by Sonells et al.

As used herein, an antenna (also called a coil element herein) is anelectrically conductive elongate body that is connected to an electriccircuit, and that (1) transmits (radiates) electromagnetic radiation(radio-frequency (RF) waves that propagate without a physical electricalconductor) corresponding to an alternating current (AC) radio-frequencysignal from the circuit, wherein the transmitted RF waves propagate intothe surrounding environment away from the coil element, and/or that (2)receives electromagnetic radiation (radio waves) from the environmentand generates an AC radio-frequency electrical signal into the circuit.Coil elements can be simply a straight, bent, or coiled piece of metalwire or rod or pipe, or a similarly shaped conductor on an insulatingsubstrate. There are a number of different types of antennae, includingmonopoles, dipoles, microstrips, striplines and slot antennae just toname a few, and various of these types of antennae can be formed intoarrays (e.g., phased arrays) to customize the shape and strength of theresulting RF field. As used herein, an “RF-coil device” or an “antennaarray” are equivalent terms for an array of coil elements (i.e., anarray having a plurality of antennae). To clarify the distinction froman inductor (i.e., an inductor which typically includes a coil of wirefor lower frequencies, and which is sometimes simply called a coil) thatis not being used as an antenna, such inductors will be called herein“inductor coils” or simply “inductors”. In some embodiments, the RF-coildevice is an MR-RF-coil device that is configured to be used in ahigh-field MR machine (i.e., it is made of non-ferrous materials and isotherwise compatible with the magnetic and RF fields typically found insuch machines) and forms an essential part of the MR machine (such as anMRI machine used to obtain images of structures inside the human body).

In conventional MR machines, there is less concern with compatibility ofthe high-power RF amplifiers to a high-magnetic-field environmentbecause in conventional MR machines the high-power RF amplifiers arelocated in a control room, and are at a distance from the remote antennaarray located in the magnet bore next to the patient.

There is a long-felt need for a more efficient and flexible way toobtain and connect high-power RF signals to one or more antenna arraysin an MR machine. This need also applies to other high-powerRF-transmit-antennae signals.

SUMMARY OF THE INVENTION

The present invention provides a more efficient and flexible way toobtain and connect high-power RF signals to RF-coil devices in an MRmachine by providing transmitter power amplifiers and/or receiverpre-amplifiers that are distributed and connected directly to the coilelements in and/or at the RF-coil device. This solution also applies toother high-power RF-transmit-antennae signals.

In some embodiments of the present invention, one or more activeelectronic devices (e.g., semiconductor devices such as field-effecttransistors, positive-intrinsic-negative (PIN) diodes, varactors(electronically variable capacitance devices), and the like) are mountedto (e.g., physically on or immediately adjacent to) a plurality of coilelements of an antenna array. In some such embodiments, the activeelectronic devices are thermally coupled directly to the antennaelements. By moving the power-amplifier circuitry from its conventionallocation somewhat distal to the coil-element array (also called theantenna array), to instead both locate the power-amplifier circuitry onthe plurality of coil elements and distribute the amplifiers across theplurality of coil elements, a number of advantages are obtained,including:

-   -   fewer and lower-power power amplifiers can be used because the        losses in the combiner and coaxial cable (frequently called just        “coax”) are avoided (this also reduces cost and reduces failure        rates by eliminating the combiners and coaxial cabling),    -   wireless connections (and/or much smaller gauge cabling) can be        used for transmit signals, as well as for receive signals, since        only low-power RF transmit signals and control signals need be        sent from the control room to the RF-coil device in the magnet        bore,    -   the coil elements provide a convenient heat-sink platform for        handling the waste heat of the power amplifiers,    -   there is more room around the patient, reducing the        claustrophobic feeling that otherwise results from the massive        cabling otherwise needed, and    -   locating the power amplifiers and/or the transmit/receive (T/R)        switches in the coil enclosure provides increased flexibility in        circuit layout and coil-element positioning, and allows        additional functionality (such as automatic tuning and impedance        matching) to be provided for the transmit circuitry and the T/R        switching circuitry.

Other advantages will become apparent to those skilled in the art uponreading the following detailed description of various embodiments.

In some embodiments, the present invention uses RF signals havingfrequencies in the range of 50 MHz to 500 MHz. In MR machines ofdifferent magnetic-field strengths, different RF frequencies are used,wherein the frequency corresponds to a nuclear resonance at a givenmagnetic-field strength; for example 64 MHz is used for MRI machineshaving 1.5-Tesla magnets (these are used for most MR machine platformsin the world today), 128 MHz is used for MRI machines having 3-T magnets(currently the fastest-growing segment of the MR market), 300 MHz isused for MRI machines having 7-T magnets (considered the highest-fieldmachines supported by industry today), 400 MHz is used for MRI machineshaving 9.4-T magnets (it is believed there are now only three in use inthe world), and 450 MHz is used for the MRI machine having a 10.5-Tmagnet (currently, just the Center for Magnetic Resonance Research(CMRR) at the University of Minnesota operates one of these).

In some embodiments, the present invention uses a plurality of Class ABpower amplifiers (e.g., each having an output stage that includes a pairof push-pull transistors that are biased to reduce the cross-overdistortion that otherwise may occur as the AC signal crosses from beingamplified by one of the transistors to being amplified by the othertransistor). Each of a plurality of transmit coil elements has its ownpower amplifier, thus distributing the power-amplifier output circuitryaround the coil. Class AB power amplifiers suffer inefficiencies due tothe fact that for significant portions of each AC RF cycle, bothtransistors are partially conducting.

To avoid such inefficiencies associated with Class AB power amplifiers,some other embodiments of the present invention instead use a pluralityof Class D power amplifiers to power amplify the Larmor-frequencyexcitation RF pulse. Class D amplifiers use duty-cycle modulation (e.g.,pulse-width modulation (PWM)) signals to drive a push-pull pair oftransistors. Other than during a very brief moment during switching,only one of the pair of transistors is “ON” while the other is “OFF,”which leads to the higher efficiencies of such power amplifiers.Typically the switching frequency is up to ten times higher than thefrequency that is to be transmitted, and the tuned circuit that the coilelement is part of will eliminate the higher switching-frequencycomponents of the output, leaving just the desired RF transmitfrequency. For example, in some embodiments, to obtain a 128-MHz RFsignal used for a 3-T MRI machine, a PWM digital signal having a1.28-GHz switching frequency (the pulse rate of the PWM source signal)may be coupled to a CMOS pair of FETs, and the output circuitry is tunedas a bandpass filter having a center frequency of 128 MHz, whicheliminates the PWM-signal's 1.28-GHz-and-higher frequency components,thus leaving the desired 128-MHz signal. For another example, in someembodiments, to obtain a 400-MHz RF signal used for a 9.4-T MRI machine,a PWM digital signal having a 4-GHz switching frequency may be coupledto a CMOS pair of FETs, and the output circuitry is tuned as a bandpassfilter having a center frequency of 400 MHz, which eliminates the4-GHz-and-higher frequency components, thus leaving the desired 400-MHzsignal. Since regular small Ethernet cabling that supports onegigabit/second signaling is readily available and Ethernet cabling thatsupports ten gigabit/second signaling is now becoming available, one cansee that very little cabling is needed to send the necessary signalsfrom the control room to the circuitry incorporated in the RF coil inthe magnet bore.

In some embodiments, the circuitry incorporated in the RF coil in themagnet bore further includes the RF oscillators needed for the transmitsignals, and thus only control signals need be sent from the controlroom to the RF coil in the magnet bore, further reducing bandwidthrequirements, and facilitating even wireless control of the RF transmitsignal. In some embodiments, wireless transmission is also used for thesignals received by the RF-coil device, and thus the only wiring neededin some embodiments is electrical-power cabling (e.g., in someembodiments, cabling for DC voltage and current) that is used to supplyelectrical power to the power amplifiers of the transmit stages, the T/Rswitches, and the pre-amplifiers of the receive stages. In some suchembodiments, cooling water is also sent to the RF-coil device to provideadditional cooling capability. In other embodiments, forced air isflowed through the magnet bore to cool the power amplifier/coilelement-heat sinks, which provides the additional advantage of providingpatient comfort.

In some embodiments, the distributed-power-amplifier apparatus of thepresent invention also includes resistors, inductors, capacitors, and/orantenna elements that have their electrical-circuit values controlled byone or more electrically controlled non-magnetic mechanical movementdevices (such as linear positioners or rotary motors (which move a solidmaterial), or pumps (which move a liquid or gas)). In some embodiments,the electrically controlled mechanical movement devices (such aspiezo-electrical linear motors, micro-electronic mechanical-system(MEMS) mechanical actuators or MEMS pumps) and other elements (which areused to make the resistors, inductors, capacitors, and/or antennaelements) include metals that have only substantially non-magneticcomponents such that the resistors, inductors, capacitors, robotic armsor similar mechanical devices, and/or antenna elements and themechanical positioner(s) or pump(s) that adjust their variable valuescan be placed and operated within and/or near an extremely high electricfield of many thousands of volts per meter (such as connected to oraffecting electricity-transmission lines carrying hundreds of thousandsof volts and very large currents), or extremely-high magnetic field suchas within the very strong superconducting-wire magnets of high-energyparticle-physics experiments (such as the Large Hadron Collider) orwithin magnets of a magnetic-resonance imaging machines, or during andafter an electromagnetic pulse (EMP) from a nuclear event.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a block diagram of a distributed-power-amplifier subsystem101 having a plurality of remote power amplifiers 108 connected to aplurality of remote antenna elements 120 and controlled from a remotecontrol room 80, according to one embodiment of the present invention.

FIG. 1B is a block diagram of a system 102 having adistributed-power-amplifier subsystem 112 having a plurality of remotepower amplifiers 107 that are driven by a remote RF oscillator 106connected to a plurality of remote antenna elements 120 and controlledfrom a remote control room 80, according to one embodiment of thepresent invention.

FIG. 1C is a block diagram of a distributed-power-amplifier subsystem110 having a plurality of remote power amplifiers 130 that are driven bya remote RF circuit 109 and connected to a plurality of remote antennaelements 120, according to one embodiment of the present invention.

FIG. 1D is a block diagram of a distributed-power-amplifier subsystem110 having a plurality of remote power amplifier-antenna portions 104that each include one or more amplifying components 129 (e.g., FETs orother transistors) and each connected to one of the plurality of remoteantenna elements 120, according to one embodiment of the presentinvention.

FIG. 2 is a block diagram of an entire system 201 according to oneembodiment of the present invention, wherein variable electricalcomponents of circuits 93A and/or 93B are controlled to parameters setby controller 203.

FIG. 3A is a block diagram of an impedance-matched high-frequencycircuit 300 according to one embodiment of the present invention, andhaving an external impedance disturbance 66 having a first effect oncircuit 300.

FIG. 3B is a block diagram of impedance-matched high-frequency circuit300, and having a different external impedance disturbance 66′ having asecond effect on circuit 300.

FIG. 4A is a block diagram of a variable antenna subsystem 401 driven bya pair of FETs having the complementary polarities (i.e., P-type andN-type) according to one embodiment of the present invention, whereinvariable antenna 420 is set to a first length.

FIG. 4B is a block diagram of variable antenna subsystem 402 driven by apair of FETs having the same polarity (e.g., both N-type in someembodiments) according to one embodiment of the present invention,wherein variable antenna 410 is set to a second length.

FIG. 4C is a block diagram of variable antenna subsystem 403 driven by apair of power-amplifier FETs, and including a receive pre-amplifier anda transmit/receive (T/R) switch to change from transmit mode to receivemode, according to one embodiment of the present invention.

FIG. 5A shows the waveforms of a control pulse used in some embodimentsto obtain a PWM seed signal.

FIG. 5B shows the waveforms of an RF sine-wave seed signal and a gatedhigher-frequency triangle or saw-tooth wave use in some embodiments toobtain a PWM seed signal.

FIG. 5C shows the waveform of a PWM seed signal.

FIG. 5D shows the waveform of an amplified PWM signal.

FIG. 5E shows the waveform of a filtered amplified RF sine-wave signal.

FIG. 6 is a flowchart of a method 600 according to some embodiments ofthe invention.

DESCRIPTION OF PREFERRED EMBODIMENTS

Although the following detailed description contains many specifics forthe purpose of illustration, a person of ordinary skill in the art willappreciate that many variations and alterations to the following detailsare within the scope of the invention. Accordingly, the followingpreferred embodiments of the invention are set forth without any loss ofgenerality to, and without imposing limitations upon the claimedinvention. Further, in the following detailed description of thepreferred embodiments, reference is made to the accompanying drawingsthat form a part hereof, and in which are shown by way of illustrationspecific embodiments in which the invention may be practiced. It isunderstood that other embodiments may be utilized and structural changesmay be made without departing from the scope of the present invention.

The leading digit(s) of reference numbers appearing in the Figuresgenerally corresponds to the Figure number in which that component isfirst introduced, such that the same reference number is used throughoutto refer to an identical component which appears in multiple Figures.Signals and connections may be referred to by the same reference numberor label, and the actual meaning will be clear from its use in thecontext of the description.

As used herein, a non-magnetic mechanical movement device is anyelectrically-controlled device (such as a linear positioner, rotarymotor, or pump) made of materials that do not move (or move to asubstantially negligible amount) due to a high magnetic field whensubjected to the high magnetic field. Such devices can be placed withinthe high magnetic field of a magnetic-resonance machine or thesuperconducting magnet of a particle accelerator without the danger ofthe device moving due to the magnetic field and/or without theundesirable result of changing the magnetic field due to their presence.In many of the descriptions herein, the term “motor” (such as motor 140)will be used as an example of such a non-magnetic mechanical movementdevice, however one of skill in the art will recognize that in otherembodiments, the “motor” can be implemented as a linear or rotary motordevice using suitable linkages, or as a pump that uses a liquid orpneumatic fluid to effectuate the described movement.

FIG. 1A is a block diagram of a distributed-power-amplifier subsystem101 having a plurality of remote power amplifiers 108 connected to aplurality of remote antenna elements 120 and controlled from a distalcontrol room 80, according to one embodiment of the present invention.In some embodiments, a controller 145 controls automatic frequencytuning and impedance matching (FIM) unit 146 (which controls impedancesand resonance frequency of the antenna elements 120 (e.g., in someembodiments, each antenna element's length is adjustable by extending aninner tube or rod 122 from an outer tube 125). In some embodiments,low-power RF and/or control signals 78 are generated in the distalcontrol room (i.e., outside the magnet room and away from the magnetbore 91) by circuit 88. In some embodiments, these signals 78 arecarried by coax, Ethernet cable, optical fibers, and/or wirelessly. Insome embodiments, signals 78 include control signals (shown as CNTL) tocontrol the switching between transmit mode and receive mode. Thereceived signals 79 from the antenna elements are obtained bypreamplifiers and receive circuit 109, and carried to outside the magnetroom to a receiver circuit 89 (e.g., in control room 80). In someembodiments, control room 80 supplies electrical power (from source 85)and/or cooling fluid or air from source 86, which power and cool thecomponents in the hybrid coil unit 111 having the distributedamplification of the RF transmit pulses.

FIG. 1B is a block diagram of a system 102 having adistributed-power-amplifier subsystem 112 having a plurality of remotepower amplifiers 107 that are driven by a remote RF oscillator 106connected to a plurality of remote antenna elements 120 and controlledfrom a remote control room 80, according to one embodiment of thepresent invention. In some embodiments, the system 102 of FIG. 1B issubstantially similar to system 101 of FIG. 1A, except that the RFtransmit signals are generated, synthesized, or sequenced in the remotecoil unit 112 (which replaces coil unit 111 of FIG. 1A). The transmitcontrol signals 69 are generated and controlled from control circuit 67.The RF transmit signal is generated by circuit 106 in the remote coilunit 112 under control of control signals 69, and drive the output stageof the distributed amplifiers 107. The received RF signals 79 fromcircuit 109 again go to the receive circuit 89, and are then processedin a conventional manner to obtain the spectroscopy or image data.

FIG. 1C is a block diagram of a distributed-power-amplifier subsystem110 having a plurality of remote power amplifiers 130 that are driven bya remote RF circuit 107 and connected to a plurality of remote antennaelements 120, according to one embodiment of the present invention. Insome embodiments, the push-pull circuitry 130 implements a Class ABtransmit output stage; while in other embodiments, it implements a ClassD (e.g., PWM) transmit output stage. In some embodiments, the automatictuning and matching of unit 146 (see FIG. 1A) is implemented using apiezo motor 140 coupled to a reference spatial location 143, andoperating a mechanical arm of a dielectric material 141, as described inU.S. patent application Ser. No. 12/719,841 by Carl Snyder et al., whichis incorporated herein by reference. In some embodiments, a power supply105 provides the electrical power to the push-pull output stage 130,while RF driver circuit 107 provides the drive signals. Other aspectsare as described above.

FIG. 1D is a block diagram of a distributed-power-amplifier subsystem110 having a plurality of remote power amplifier-antenna portions 104that each include one or more amplifying components 129 (e.g., FETs orother transistors) and each connected to one of the plurality of remoteantenna elements 120, according to one embodiment of the presentinvention. In some embodiments, each power-amplifier-antenna portion 104obtains electrical power from a voltage supply 105, and drive signalsfrom a Class D driver circuit 107. FETs 129, in some embodiments, areCMOS pairs, while in other embodiments, FETs having the same polaritytype are used. In some embodiments, FETs 129 are mounted on the basepart 125 of antenna 120, which also includes a movable part 122 (asdescribed above and shown in FIG. 1A). In some embodiments, overall coilcontroller 145 operates the circuitry shown under control of a signal 77received through wired or wireless control and/or RF transceiver circuit115 from a distal circuit in control room 80 outside the magnet room. Insome embodiments, FIM circuitry 149 includes a plurality of switchedresistance, inductance and/or capacitance (RLC) circuitry to match thefrequency and impedance desired. In some embodiments, an automatictuning circuit 146 controls the operation of the antenna adjustment rod(controlling the length of the antenna 125-122) and the PIN-switched RLCelements 149 that are coupled to the various parts and transmissionlines in each portion 104. In some embodiments, the transmit/receive(T/R) switch and preamplifier 109 receives the resulting relaxationsignal from the antenna element(s) and provides parallel wired orfiber-optic output signals 77 (through wired or wireless control and/orRF transceiver circuit 115, which is used for transmit and/or receivesignals) to the control room 80. In some embodiments, cooling and power84 are supplied from outside the magnet room.

FIG. 2 is a block diagram of an entire system 201 according to oneembodiment of the present invention, wherein variable electricalcomponents of circuits 93A and/or 93B (particularly those in the portionlabeled 93A in a remote environment 202) are controlled to values set bycontroller 245. In some embodiments, the frequency-impedance-matching(FIM) circuit has two portions, a first portion 93A that is remote(i.e., located at a distance, e.g., in the high-field magnet located ata distance from the control room 80 of an MRI system) from a secondportion 93B (e.g., the portion located in the control room 80). In someembodiments, remote circuit portion 93A is coupled to circuit portion93B by a transmission line 219 (having a characteristic impedance Z at agiven operating frequency or spectrum) such as a coaxial cable. Inconventional systems, the frequency and impedance of the remote antennaarray would need to be matched to the impedance of the coax cable 219.However, in some embodiments of the present invention, the remotedistributed amplifier 107 provides a buffer, wherein the signal comingfrom the distal control room 80 and through the cable 219 sees only theinput impedance of the amplifier and the effect of the variabledisturbance on that impedance is negligible or substantially zero. Thus,even in embodiments having the RF-transmit signal generated in thedistal control room 80, there is less of a requirement to matchimpedance of the coax cable 219 due to changes in the variabledisturbance (e.g., the variations of patient weight, size, orcomposition). Further, in some embodiments, the signal sent across cable219 is a duty-cycle-modulated (DCM) signal (in some embodiments, the DCMsignal is a pulse-width-modulated (PWM) signal, while in otherembodiments, pulses having a substantially unchanging pulse width buthaving a variable frequency, or other DCM characteristic are used). Instill other embodiments, the signals on cable 219 include relativelylow-frequency control signals (e.g., digital pulses that control thetiming and duration of the transmitted RF pulses and the switchingoperations that control reception of the resulting RF response from thesubject in the MR magnet, for example that control operation of an RFoscillator and pulse generator that are both in the remote device 202,and switching PIN-diodes that isolate the RF-reception preamps of thereceive portion of the remote device 202).

In some embodiments, controller 203 is well outside of the remoteenvironment 202 (such as a high magnetic field enclosure, or a broadcasttelevision antenna on a tower, or a remote weather sensor) that includescircuit portion 93A and its RLC components controlled by piezo motor 240and/or its controller rod 239. In other embodiments, both portions 93Aand 93B of the circuit (which includes both circuit portions 93A and93B, as well as the FIM controller 245 and its impedance detector 241,VSWR detector 242, and frequency detector 243) are in the remotelocation in device 202. The FIM controller 245 provides the controlsignals that vary the antenna length(s) of antenna 120 and/or thevariable R, L, and/or C values in circuit 93A, in order to match thedesired resonance frequency of the RF transmitter to the desiredtransmit frequency (which, in some embodiments, is determined by the PWMsignal that is Class-D amplified and filtered to form the RF transmitpulse). In some embodiments, electrical circuit 93B includes aradio-wave transmitter, receiver, or both (including the distributedpower amplifier circuits 107 and antennae 120).

One use of the present invention is to provide remote amplification ofthe transmit RF pulse (e.g., a plurality of cycles of an RF signal gatedby a signal that determines the length of the pulse (i.e., how many RFcycles are transmitted)) and to balance (match the resonance frequencyand impedance) an RLC circuit (that includes antenna elements) whereinthe inductance and/or capacitance parameters of at least a portion ofthe RLC circuit is affected by an external and variable disturbance 66such as weather conditions or a conductive and/or dielectric body (e.g.,such as when the frequency and/or impedance in relation to atransmission-line-signal connection of the circuit must be maintainedfor optimal performance, but the environment changes over time), whereinthe variable disturbance 66 must be accommodated by changing thevariable inductor and/or the variable capacitor. Accordingly, in someembodiments, an impedance-mismatch detector 241 and/or avoltage-standing-wave-ratio (VSWR) detector 242 are used to determinewhether and how to modify the values of the inductance and capacitancein order to rebalance the impedance. For example, if circuit portion 93Ahas power amplifier output stages 107 (see FIG. 1D) each having acharacteristic impedance Z₀ and a characteristic frequency F₀, andtransmit antenna elements 120 each have the same characteristicimpedance Z₀, then the transmit circuit would be considered balanced.Similarly if the receive-preamplifier input stages 109 (see FIG. 1D)each have a characteristic impedance Z₀ and a characteristic resonancefrequency F₀, and receive antenna elements 120 each have the samecharacteristic impedance Z₀, then the receive circuit would beconsidered balanced. In some embodiments, the characteristic RLC valuesalso determine a characteristic frequency F₀ or characteristic Q₀ (thequality of a resonant circuit). If then the variable disturbance 66modifies the characteristic impedance of circuit portion 93A to achanged characteristic impedance Z₀+AZ, then impedance-mismatch detector341 and/or a voltage-standing-wave-ratio detector 342 would detect thechange, and they send signal(s) to motor controller 245, which causesmotor 240 to modify the variable portion(s) of capacitance and/orinductance to rebalance the impedances of each portion. If then thevariable disturbance 66 changes and modifies the characteristicfrequency F₀ or characteristic Q₀ of circuit portion 93A (by changing anRLC parameter) combined with circuit portion 93B to a changedcharacteristic frequency F₀+ΔF or characteristic Q₀+ΔQ, then frequencydetector 243 and/or a Q detector (not shown) would detect the change,and they send signal(s) to motor controller 245, which causes motor(s)240 to modify the variable portion(s) of capacitance and/or inductanceto reset the frequency and/or Q of each portion.

In some embodiments, each of the components including the poweramplifier 107 within remote environment 202 is made of materials that donot contain combinations of iron, nickel, cobalt, or the like that maybe moved (physically displaced) by the high field, in order that thehigh field does not move these components.

In some embodiments, all or the relevant components including thedistributed power amplifiers are in a single location, and the presentinvention is used to adjust component parameters to compensate for someenvironmental change or a change in the physical surroundings of thecircuit that affected any of the RLC parameters. For example, the merepresence of a person or other modality (that might be used to tune someaspect of a circuit) might adversely affect a resistance, inductance orcapacitance. In those cases, some embodiments of the inventionfacilitate the adjustment of the resistance, inductance or capacitancevalues without a person needing to be in the vicinity. As anotherexample, some circuits may need to be tuned to have a certainresistance, inductance and capacitance in the presence of a person(where a person in the vicinity changes these parameters by theirpresence, or due to physical or physiological motion (e.g., breathing,heart beating, gastrointestinal movement, and the like) by the person),but the position, body composition and size of the person is unknown andmust be compensated for, and some embodiments of the inventionfacilitate the adjustment of the resistance, inductance or capacitancevalues to automatically compensate for those characteristics of theperson in the vicinity. In some embodiments, conventional magnet-basedmotors or electric-field based motors themselves would have an undesiredeffect on the resistance, inductance and capacitance of a sensitivecircuit (or such motors could themselves be adversely affected by highmagnetic or electric fields), so piezo-electric motors as describedherein have the advantage of not interacting (or interacting verylittle) with the resistance, inductance and capacitance being adjusted.

FIG. 3A is a block diagram of an impedance-matched high-frequencycircuit 300 according to one embodiment of the present invention, andhaving an external impedance disturbance 66 having a first effect oncircuit 300. In some embodiments, a driver circuit 320 has acharacteristic impedance Z₁ composed of (or modeled by) an equivalentcapacitance 321, equivalent inductance 322, equivalent resistance 323,and ideal voltage source driver 345 (which outputs a voltage signalhaving one or more frequency components and optionally a DC component,but is modeled as having a very high or infinite impedance such that itsimpedance does not affect the circuit). In other embodiments, idealvoltage source driver 345 is replaced by an ideal voltage sensor ortransceiver (transmitter-receiver combination) (having a very high orinfinite impedance such that its impedance does not affect the circuit).Of course, in other embodiments, the parallel connection of equivalentcapacitance 321, equivalent inductance 322, equivalent resistance 323and low-power RF driver voltage source 345 can be replaced with aseries-wired connection of a capacitance, inductance, resistance and anideal current source (and/or ideal current detector, each having zero ornegligible impedance) that can provide the same characteristic impedanceZ₁. Driver circuit 320 is electrically coupled to a transmission linesegment 330 (i.e., of transmission line 219 as shown in the othervarious Figures herein) also having the characteristic impedance Z₁ atthe respective frequencies of interest in the signal, and transmissionline segment 330 is in turn electrically coupled to the input port (alsohaving the characteristic impedance Z₁ at the respective frequencies ofinterest in the signal) of a remote amplifier 307 whose output (having acharacteristic impedance Z₀ at the respective frequencies of interest inthe signal) is connected to a tuned circuit 310, which, in someembodiments, includes an equivalent capacitance (that includes a fixedcapacitance component 311 and a variable capacitance component 301 thatcan be tuned as described in U.S. patent application Ser. No. 12/719,841titled “REMOTELY ADJUSTABLE REACTIVE AND RESISTIVE ELECTRICAL ELEMENTSAND METHOD” filed 8 Mar. 2010, which is incorporated herein byreference, and which issued as U.S. Pat. No. 8,299,681 on Oct. 30,2012), an equivalent inductance (that includes a fixed inductancecomponent 312 and a variable inductance component 302 that can be tunedas described in U.S. patent application Ser. No. 12/719,841), and anequivalent resistance (that includes a fixed resistance component 313and a variable resistance component 303 that can be tuned as describedin U.S. patent application Ser. No. 12/719,841).

In some embodiments, the characteristic impedance Z1 of low-power RFdriver 345 and its equivalent capacitance 321, equivalent inductance322, and equivalent resistance 323 matches the characteristic impedanceZ1 of cable 330 and the characteristic impedance Z1 of the input port ofremote power amplifier 307. Also, in some embodiments, thecharacteristic impedance Z0 of the output port of remote power amplifier307 matches the characteristic impedance Z0 of the antenna element 310in the presence of variable disturbance 66. Note that in someembodiments, Z1 is designed to be equal to Z0 for convenience, while inother embodiments, Z1 is set to a first value that is easiest to meetfor a given RF driver 345, cable 330 and the input impedance of poweramplifier 307, while Z0 is set to a value that is more convenient formeeting given the output impedance of power amplifier 307, and thecharacteristic impedance of the output resonant-filter frequency andantenna array elements 304.

In some embodiments, detector-controller 203 is physically located inthe distal control room 320, and measures and controls the Z₀ from thisdistal location, as shown in FIG. 3A. When in the distal location,detector-controller 203 need not be high-field compatible. In otherembodiments, detector-controller 203 is physically located in the remoteenvironment 310, and measures and controls the Z₀ from this location inremote environment 310. When in the remote environment 310,detector-controller 203 should be high-field compatible (e.g., madecompletely of non-ferrous materials). In some embodiments, having thedistributed power amplifier 307 as well as the variable components 301,302, and 302 all located in the remote environment 310 may make it mostconvenient to also locate the detector-controller 203 in the remoteenvironment 310 adjacent the parts it is measuring and controllingrather than in the distal control room 320.

In some embodiments, at least one variable antenna element 304 isincluded (e.g., in some embodiments, coupled to the upper nodes ofvariable capacitor 301, variable inductor 302, and variable resistor302, wherein the physical length, position and shape of one or moreantenna elements are varied (such as described in U.S. patentapplication Ser. No. 12/719,841 titled “REMOTELY ADJUSTABLE REACTIVE ANDRESISTIVE ELECTRICAL ELEMENTS AND METHOD” filed 8 Mar. 2010, which isincorporated herein by reference, and which issued as U.S. Pat. No.8299681 on Oct. 30, 2012) under the control of detector-controller 203shown in FIG. 2). In some embodiments, when in the presence of avariable disturbance 66 having a first characteristic (such as a pieceof material, a person, or a weather situation), the capacitance,inductance and/or resistance of tuned circuit 310 are adjusted byvarying the variable aspects of variable capacitance component 301,variable inductance component 302 and variable resistance component 303using one or more sensing units (such as detectors 241, 242 and 243 ofFIG. 2) and one or more motor controllers 145 and motors 140 (see FIG.1C). In some embodiments, a detector-controller 201 (which may includecircuit and/or microprocessor components, such as described above forFIG. 2) is coupled (e.g., in some embodiments, connected to transmissionline 219) to measure electrical parameters of the signals (e.g., at theleft end of transmission line 219), and based on the measurement(s), tocontrol the variable parameters (e.g., resistance, inductance,capacitance, antenna length, resonant frequency, impedance at a givenfrequency, field shape, field direction, field spatial shape, fieldintensity, and like characteristics) in the remote tuned circuit 310.

FIG. 3B is a block diagram of impedance-matched high-frequency circuit300, and having a different external impedance disturbance 66′ having asecond effect on circuit 300 (e.g., adding some impedance offset ΔZ suchthat the impedance of circuit 310 without compensation would be Z0+ΔZ).In some embodiments, the present invention is used to adjust the RLCparameters of variable components 303, 302 and 301 and optionally thelength of antenna 304 in order to subtract a compensating impedance(−ΔZ) rebalance the circuit 310′ to again have the characteristicimpedance Z0 (=Z0+ΔZ−ΔZ) that matches the output impedance of the remotepower amplifier 307 (in terms of characteristic impedance, frequency, Q,and/or other factor) in the presence of the changed external impedancedisturbance 66′. In some embodiments, the present invention provides thecapability to automatically adjust such parameters in the adjusted tunedcircuit 310′ “in real time” (i.e., quickly as the external impedancedisturbance 66′ changes over time).

FIG. 4A is a block diagram of a variable antenna subsystem 401, whereineach antenna element 420 is driven by its own pair of FETs having thecomplementary polarities (i.e., P-type and N-type) according to oneembodiment of the present invention, wherein variable antenna element420 is set to a first length, and CMOS FETS 412 and 413 are mounted onantenna element 420 for better impedance matching and heat-control. Asdiscussed above, some embodiments include the detector-controller 203 inthe control room 80 (distal from the distributed power amplifier 410).In some embodiments, the distributed power amplifier 410 includes aClass D RF driver 416 for CMOS output transistors (P-type FET 412 andN-type FET 413), and provides a duty-cycle-modulated (DCM) signal (e.g.,in some embodiments, a PWM signal) that when filtered by the antenna andits variable RLC circuit 117, produces the desired RF pulse (whichincludes a plurality of cycles of RF radio waves (e.g., radio wavestuned to a Larmor frequency) used to excite thenuclear-magnetic-resonance (NMR) response in the tissues of thepatient). In some embodiments, the variable RLC circuit 117 and antenna420's length are controlled by detector-controller 203 in the controlroom 80, while in other embodiments, variable RLC circuit 117 andantenna 420's length are controlled by frequency-impedance matching(FIM) circuitry (equivalent to detector controller 203) that is withinthe MR magnet bore 91. In some embodiments, each of a plurality ofantenna elements 420 has its own power amplifier and impedance-matchingcircuitry 404 (e.g., shown as 404, 404.1, through 404.2), and in someembodiments, they share a common RF oscillator 415 (or PWM-signalsource) and a common power supply 105 (which may include a voltage orcurrent source). In some embodiments, the control signal 77 includes awireless link, while in other embodiments, a wired (e.g., coax or10-gigabit category 6A cable or the like). Because the poweramplification is done in the remote environment 202, the need forvery-high-power coax (conventional systems may need coax capable ofcarrying 30 kW or more) is reduced or eliminated, and wirelesscommunication of the low-power RF signal or even just generation of alocal RF signal in the remote environment 202 can be done wirelessly.

FIG. 4B is a block diagram of variable antenna subsystem 402, whereineach one of a plurality of antennae is driven by a pair of FETs havingthe same polarity (e.g., both N-type in some embodiments) according toone embodiment of the present invention, wherein variable antenna 410 isset to a second length. This subsystem 402 is substantially similar tosubsystem 401 of FIG. 4A, except that the CMOS pair of transistors 412and 413 is replaced by a pair of NMOS transistors 413 and 413′, and theClass D RF driver 416 for CMOS output transistors has been replaced by aClass D RF driver 417 for NMOS output transistors (N-type FET 413′ andN-type FET 413), and provides a bias-adjusted (biased to provide theproper voltages for turning one transistor completely off when the othertransistor is completely on) DCM signal (e.g., in some embodiments, aPWM signal) that when filtered by the antenna and its variable RLCcircuit 117, produces the desired RF pulse (a plurality of cycles of RFradio waves used to excite the nuclear-magnetic-resonance (NMR) responsein the tissues of the patient), and provides a duty-cycle-modulated(DCM) signal (e.g., in some embodiments, a PWM signal) that whenfiltered by the antenna and its variable RLC circuit 117, produces thedesired RF pulse (a plurality of cycles of RF radio waves used to excitethe nuclear-magnetic-resonance (NMR) response in the tissues of thepatient). In the embodiment shown, the length of antenna element 420 isshown as adjusted (lengthened to configuration 420′ in this case).

FIG. 4C is a block diagram of variable antenna subsystem 403, whereineach one of a plurality of antennae is driven by a differenttransmit-amplifier and receiver-pre-amplifier unit 430. In someembodiments, unit 430 includes a power amplifier (e.g., driver 416 andone or more transistor(s) 412-413), a receive pre-amplifier 433, and atransmit/receive (T/R) switch 431 used to change from transmit mode toreceive mode, according to one embodiment of the present invention. Insome embodiments, the heat-generating elements (e.g., the power FETS412-413) are mounted on and/or thermally connected to antenna element420 for better impedance matching and heat-control. As discussed above,some embodiments include the detector-controller 203 in the distalcontrol room 80 (distal from the distributed power amplifier andreceiver preamp unit 430). In some embodiments, the distributed poweramplifier 430 includes a Class D RF driver 416 for CMOS output P-typeFET 412 and N-type FET 413, such as shown in FIG. 4A and describedabove. In other embodiments, rather than using a Class D power amplifieras shown here, other types of RF power amplifiers are used, includingClass A, Class AB, or other suitable types. Although shown here asincluding a p-FET 412 and n-FET 413, the output stages in otherembodiments include any other suitable electronic or opto-electronicamplifier devices. In some embodiments, the variable characteristics ofRLC circuit 117 and antenna 420's variable length are controlled bydetector-controller 203 in the control room 80, while in otherembodiments, variable RLC circuit 117 and antenna 420's length arecontrolled by frequency-impedance matching (FIM) circuitry in coilcontroller 435 (in some embodiments, equivalent to that which isotherwise included in detector controller 203) that is within the MRmagnet bore 91. In some embodiments, each of a plurality of antennaelements 420-420.2 has its own power amplifier and impedance-matchingcircuitry 430-430.2 respectively, and in some embodiments, they share acommon RF oscillator 415 (or PWM-signal source) and a common powersupply 105 (which may include a voltage or current source). In someembodiments, the control signal 77 includes a wireless link, while inother embodiments, a wired (e.g., coax, 10-gigabit category 6A cable orthe like) or optical fiber is used for carrying the control and/or RFsignals. Because the power amplification is done in the remoteenvironment 202, the need for very-high-power coax (conventional systemsmay need coax capable of carrying 30 kW or more) is reduced oreliminated, and wireless communication of the low-power RF signal oreven just generation of a local RF signal in the remote environment 202can be performed and controlled wirelessly. In some embodiments, thelow-power DCM signal pulses (which can be up to 4.5 GHz or higher) aregenerated in circuit 434 in the remote environment 202. In otherembodiments, these DCM pulse streams are generated in the control room80 (or elsewhere away from the magnet bore) as low-power electricalsignals, and are carried to subsystem 403 via low-power coax orhigh-speed Ethernet cabling (wherein such electrical cabling is made ofpolymers, copper or other high-field MR-compatible materials).

In still other embodiments, these DCM pulse streams are generated in thecontrol room 80 (or elsewhere away from the magnet bore) as opticalsignals, and are carried to subsystem 403 via optical fiber. In somesuch embodiments, DCM RF driver 416 converts the optical signals toelectrical pulses that drive the output FET(s) 412-413. Note that inembodiments using Class AB or other types of output stages, the opticalsignal may represent the actual RF cycles of the desiredLarmor-frequency excitation pulse. In some embodiments, the opticalsignal (or other low-power signal) is pre-distorted in order tocompensate for characteristics of the power-amplifier circuitry inportion 404, in order to obtain the desired high-power RF output signal.

In some embodiments, each set of output transistor(s) 412-412 aredirectly connected to their respective antenna element 420 using veryshort leads, to reduce mismatched impedances. In other embodiments, T/Rswitch 431 includes a multiple-pole electronic switch or RF relay (e.g.,in some embodiments, including PIN diodes or other suitable switchingdiodes such as described in U.S. Pat. No. 4,763,076 to Arakawa et al.(incorporated herein by reference)) that switches from a transmit stateor mode to a receive state or mode. In transmit mode, the output of thepower amplifier (having an output impedance that matches the impedanceof antenna 420) is coupled to antenna 420 to transmit its output signal,and simultaneously the input to the preamp 433 is disconnected from theantenna and instead is coupled to a matched terminating impedance (aterminating impedance that matches the input impedance of the preamp433) such that substantially no signal gets coupled to the input ofpreamp 433. In receive mode, the input to the preamp 433 is coupled toantenna 420 to receive its input (received) signal, and simultaneouslythe output of the power amplifier is disconnected from the antenna andinstead is coupled to a matched terminating impedance (a terminatingimpedance that matches the output impedance of the power amplifier 410)such that substantially no signal from the power amplifier getsinadvertently coupled to the input of preamp 433 (and in someembodiments, both FETs 412 and 413 are turned off (to a high impedancestate)). When in receive mode, the circuit disconnects or disables theRF source signal from the input of the driver circuit 416. In someembodiments, a second T/R switch (not shown) similar to T/R switch 431described above is used, when in the receive state, to disconnectsignals from the input of driver 416 and to instead connect a matchedtermination impedance 437 to the input of driver 416, but when in thetransmit state, connect signals from circuit 434 to the input of driver416 and the impedances of these are matched to one another. In otherembodiments, the second T/R switch is omitted. In some embodiments,controller 435 supplies control signals to control the switching of T/Rswitch 431 and/or the second T/R switch and/or driver 416 (in order toturn off both FETs 412 and 413 when in receive mode).

In some embodiments, controller 435 supplies control signals tofrequency-and-impedance-matching (FIM) circuit 117 (in order to adjustimpedances of the various transmission-line elements that carry signalsfrom one output to another input to match one another, and to match theresonance frequencies of various elements to the desired transmit orreceive frequencies) and receives and measures appropriate sense signals(e.g., to measure voltage-standing-wave ratios (VSWRs) or other suitableparameters, in order to control the FIM operations).

FIG. 5A shows the waveforms of a control pulse 500 used in someembodiments to obtain a PWM seed signal. In some embodiments, controlpulse 500 determines the start time and duration of the output RF pulse505 (see FIG. 5E).

FIG. 5B shows the waveforms of an RF sine-wave seed signal and a gatedhigher-frequency triangle or saw-tooth wave use in some embodiments toobtain a PWM seed signal. In some embodiments, these two signals arecompared such that for each time period when the triangle wave isgreater than the sine wave, a pulse is generated. The resulting PWMpulse stream 503 is shown in FIG. 5C.

FIG. 5C shows the waveform of a PWM seed signal 503. In someembodiments, this signal is generated as described in FIG. 5B. In otherembodiments, other ways of generating a comparable waveform are used(e.g., cyclic digital oscillators, table lookup from a high-speed memoryor the like).

FIG. 5D shows the waveform of an amplified PWM signal 504. Because ofthe rise and fall times of this signal being much faster than the dv/dt(change in voltage over time) of the RF sine wave, the efficiency of aClass D power amplifier is greater than alternatives such as a Class ABpower amplifier. This PWM signal is then fed to a high-Q resonator thatincludes the antenna element (e.g., circuit 117 and antenna 420 of FIG.4A or 4B), which performs a narrow-bandwidth bandpass filter functionand outputs the signal shown in FIG. 5E.

FIG. 5E shows the waveform of a filtered amplified RF sine-wave signal505 resulting from the process described for FIGS. 5A-5D above.

FIG. 6 is a flowchart of a method 600 according to some embodiments ofthe invention. In some embodiments, method 600 starts by selecting 610one or more (e.g., in some embodiments, a plurality of) criteria (insome embodiments, parameters such as impedance and frequency, in otherembodiments, any other desired condition) to optimize. Next, a circuit(e.g., under control of non-magnetic mechanical movement devices)performs configuring 611 for excitation (e.g., transmitting to orreceiving from) the remote circuit elements. In some embodiments, the RFexcitation signal is power amplified 620 by a power amplifier located onor next to the antenna element, and filtered 621 at the high-Q antenna.The next block includes delivering 612 the excitation (radiating the RFradio waves in the MR magnet bore). The next block includes detecting614 a received signal from the remote elements. The next block includeschecking 615 for satisfactory parameters (e.g., the impedance andfrequency of the signal) of the received signal from the remoteelements. If the result is unsatisfactory, the method then includesadjusting 617 one or more of the variable reactance elements using thenon-magnetic mechanical movement device(s) and going to block 611 toiteratively repeat the process 611 through 615. If the result ofchecking 615 is satisfactory, the method goes to performing 616 theoperation for which the components were adjusted (e.g., obtaining amagnetic resonance result (such as an image).

In some embodiments, the present invention uses distributed poweramplifiers along with electronically controlledfrequency-impedance-matching circuits (e.g., PIN diode-controlledcapacitances and/or inductances and/or antenna lengths) and/or variableresistors, inductors and/or capacitors that have theirelectrical-circuit values controlled by one or more electricallycontrolled mechanical positioners. In some embodiments, the distributedpower amplifiers and electronically controlled FIM circuits includemetals that have only substantially non-magnetic components such thatthe resistors, inductors and/or capacitors and the mechanicalpositioner(s) that adjust their variable values can be placed andoperated within and/or near an extremely high electric field of manythousands of volts (such as connected to or affectingelectricity-transmission lines carrying hundreds of thousands of voltsand very large currents), or extremely-high magnetic field such aswithin the very strong superconducting-wire magnets of high-energyparticle-physics experiments (such as the Large Hadron Collider) orwithin magnets of a magnetic-resonance imaging machines, or during andafter an electromagnetic pulse (EMP) from a nuclear event.

Some embodiments of the invention include an apparatus that includes anon-magnetic positioner, and an electrical component connected to themotor and configured to have at least one of its parameters varied bythe positioner. In some embodiments of the apparatus, the positionercomprises a piezo-electric motor. In some embodiments of the apparatus,the electrical component includes an inductor, and wherein the at leastone of its parameters includes an inductance. In some embodiments of theapparatus, the electrical component includes a capacitor, and whereinthe at least one of its parameters includes a capacitance. In someembodiments of the apparatus, the electrical component includes aresistor, and wherein the at least one of its parameters includes aresistance. Some embodiments further include a programmableinformation-processing device operatively coupled to control thepositioner in order to vary an electrical parameter of the electricalcomponent. Some embodiments further include a feedback circuitoperatively coupled to the programmable information-processing device toprovide feedback control of the positioner in order to maintain theelectrical parameter of the electrical component.

Some embodiments of the invention include an apparatus that includes anelectrical component, and means, as described and shown herein andequivalents thereof, for automatically adjusting its impedance.

In some embodiments, the method of the present invention is executed ona computer at a location remote from a user, and controlled by the useracross the internet. In some embodiments, the method is executed on acomputer at a location remote from the variable electrical components.In some such embodiments, the method is controlled by the computeracross a network.

In some embodiments, the present invention includes one or more of anyone or more of the devices in any of the figures herein in a combinedcircuit that connects the described variable components and distributedpower amplifiers, optionally including other conventional components. Insome embodiments, the present invention provides an RF coil for MRI orEPR (electron paramagnetic resonance) spectroscopy or imaging, or anyother antenna, wherein a combination of coil and amplifier-places the RFpower amplifier for the system out of external box (the circuitry in thedistal control room) and instead distributes the power amplificationover the body of the coil (e.g., placing a power amplifier at or on eachof a plurality of antenna elements). In the old days, push-pull tubes ordistributed solid-state designs involved buying very many power FETS tocombine efficiently two to four FETs per board to get 450-500 Watts perboard, then combine boards with more combiners to get 20 kW to 40 kW(standard is 35 kW) needed for MRI's RF pulse signal. Typically such abox is located outside the MRI magnet room. It incurs lots of loss inthe combining and then more in cables and coils in the magnet. The costof such a power amp is second only to the cost magnet in the expense ofbuilding an MRI machine. The expensive cabling is type-rg214 or rg400cables from the combined output of multiple power amplifiers and thedistributed to multiple antennas.

In contrast, the present invention provides power FETs, one or more pereach of a plurality of coil elements, and thus the present invention canomit combiners-mount one FET amplifier per coil element. In someembodiments, it uses the coil elements for the heat sink of the poweramplifiers, and distributes the heat over the coil, which in variousembodiments, includes any multiple-element coil. In some embodiments,the coil includes a body, head, or surface coil for an MRI machine. Insome embodiments, the RF and/or control send signals wirelessly or oversmall cables or over optical fibers. The present invention provides, forthe first time, a capability to wirelessly send or control the RF to thetransmit coils. In some embodiments, dedicated amplifiers are providedfor dedicated elements. The present invention facilitates manipulationof the field to use for B₁ shimming or transmit-sense functionality. Thepresent invention provides better imaging since it easily switches fromdifferent subsets of the multiple individually controlled elements tochange the transmitted signal's phase, magnitude, spatial profile (fieldshape in space), temporal profile (pulse shape in time), and frequency(all controllable as independent variables), in order to optimize thesignal to particular position of interest (VOXEL), to maximizesignal-to-noise (SN) and/or contrast and/or spectral and/or spatialresolution, as well as minimizing specific absorption rate (SAR) andheating of the patient and components in the magnet bore. The presentinvention provides better performance through parallel imaging (thissaves time especially), especially when using parallel transmit signals(e.g., in some embodiments, using a plurality of parallel optical fibersto carry the transmit signals (e.g., either the DCM pulses to drive aClass D output that then filters to obtain the RF transmit pulse, or theRF pulse itself for a Class AB output, and optionally pre-compensates ordistorts the signal on the optical fiber), or RF paralleltransmit-receive. In some embodiments, the present invention providestransmit sense capability (which transmits different pulse widths overdifferent antenna elements). In some embodiments, this provides RF-fieldfocussing and optimization.

In some embodiments, the present invention gets receive signals frommultiple antenna elements in parallel, generates and carries these aselectrical or optical signals to the distal control room, then combinesthese signals (externally to the magnet room). In some embodiments, theapparatus transmits signals from many of elements simultaneously, whichsaves time on spatial encoding. In some embodiments, speed-up oracceleration factors of 5-6 times or more are obtained for given imageor given quality from this parallel imaging. The present inventionprovides faster MRIs, a better control over RF to the region ofinterest, uses higher frequencies for better S/N, and controls shimfields better. In some embodiments, the present invention provides abetter coil that includes both parallel transmit or paralleltransmit-receive in the RF coil itself.

In some embodiments, the present invention provides one or more of thefollowing features and/or advantages:

-   -   distributed receive amplifiers at T/R switches in coil    -   power amplifier distributed over coil, with 1 or more FETS on or        near coil element    -   support for various coil elements stripline, loop, dipole        antenna, monopole antennas    -   connection methods between power amplifier and antenna elements        include wirebond, solder directly to it, mount FET chip directly        to coil element, screw stud of FET into end or side of antenna        element.

In some embodiments, a wireless transmit coil that has wireless receiveron the element in magnet to obtain better S/N, which still needs a DCpower cable that is relatively small out-of way wires rather than hugeRF power coax cables. In some embodiments, it may have other controllines to FET like T/R switch control. There are lots of ways ofexecution. In some embodiments, 16 or 32 parallel rods in cylindricalcoil unit are used—the antenna elements can include cylindrical orcoaxial-adjustment antenna elements. The entire coil can be a volumecoil (cylindrical or ellipsoidal or other odd shapes) or just surroundvolume as a surface (flat or curved plane(s)) coil. The power amplifiercan mount on end (voltage source for half-wave capacitively shortenedresonator or stripline or microstrip or coaxial line) or center (currentsource for dipole antenna.) The elements can be arranged as any otherarray form with antenna elements displace in XY or XYZ directions. Insome embodiments, the present invention provides a pair of arrays thatare end-to-end to one another. The present invention facilitates moregeometries because there is more real estate (volume room). Other thingsthat are dedicated on, at or near element:

power amplifier (power FET)

preamp GAAS FET

pin diode switch

T/R switch (PIN)

wireless receiver—RF input to transmitter)

wireless transmitter—get signal from preamp and send to external

wireless controls—control PIN switch to tell when to switch

to turn power amp on-off, pr receiver on-off (or “blank” one or both)

hardwire or program on-board memory to drive long pulse sequences atchip

active tuning-smart VSWR tuning or go back to through wireless or wiredcontrol to console computer (auto tuning or matching).

In the past, the only elements were preamps or PIN switching of xmit(transmit)-receive or detune receive element during transmit so itdoesn't receive what is being transmitting. In some embodiments, thepower amplifier FETs-commonly M150 (Motorola 150-Watt) and up to 1.2 kWare used. In a 16-element coil, that provides 16 kW at same time (shouldbe far cheaper and far more efficient than sending 30 kW from outsideroom). The power FET on board gives you all the other features such aswireless transmit. In some embodiments, the present invention providescooling water or other cooling fluid, or air (fans), especially if wehave high efficiency amplifiers (can go to 32, 64, or 128 elements), anddistribute heat over many elements and air though coil. The gradientcoils are cooled with water. In some embodiments, the invention embedsthe RF coils into magnet or insert into magnet with the patient.

In some embodiments, the RF coil unit size is the diameter of the MRIbore (standard bore inside magnet inside Faraday cage industry body coil65-70 cm in diameter, wherein the active circuit is in range 15-18 cmlong to 60 cm long. Head coils are 24-28 cm in diameter and circuitlength (element lengths 15-30 cm long-15-25 cm usually). Someembodiments include 8-16-24-32 elements for head coils, body coils are 8or 16 elements usually, but can have 128 elements. In some embodiments,the number of antenna elements could be non-power-of-two. In someembodiments, digital control elements can adjust gain at power-of-twofactors (mostly computer memory and control lines on the receive tosample directly into memory. Some embodiments include sending pulsesequences at 64 MHz. Can simultaneously xmit (transmit) and receiveusing a circulator xmit (transmit) 120 degrees to element 240 degrees toreceiver (typical existing circulators are problematic-cannot useferrites in magnet) so the present invention uses a ¼-wave circulatorwaveguide but that is perhaps too big to put into magnet. Someembodiments further include a stripline transmission-line circulator.

In some embodiments, the present invention provides a method thatincludes: providing an MRI coil having a plurality of antenna elements,including a first antenna element and a second antenna element; locatingthe MRI coil in a bore of an MR magnet; based on a control signal from alocation remote from the plurality of antenna elements, power amplifyinga first RF pulse to obtain a first high-power RF pulse and poweramplifying a second RF pulse to obtain a second high-power RF pulse; andcoupling the first high-power RF pulse to at least the first antennaelement but not to the second antenna element and coupling the secondhigh-power RF pulse to at least the second antenna element but not tothe first antenna element, wherein the power amplifying is performed inthe bore of the MR magnet. Some embodiments of the method furtherinclude coupling heat from the power amplifying the first RF pulseprimarily to the first antenna element, and coupling heat from the poweramplifying the second RF pulse primarily to the second antenna element.In some embodiments of the method, the first RF pulse has a power ofless than one watt and the first high-power pulse has a power of atleast 100 watts. In some embodiments of the method, the first RF pulsehas a power of less than one watt and the first high-power pulse has apower of at least 1000 watts. Some embodiments of the method furtherinclude electrically controlling an impedance of the first antennaelement to match an impedance of the power amplifying. Some embodimentsof the method further include using a programmableinformation-processing device operatively coupled to control operationof the power amplifying in the MRI coil from a location at least onemeter away from the MRI coil. Some embodiments of the method furtherinclude: electrically controlling an impedance of the first antennaelement to match an impedance of the power amplifying; and using afeedback signal operatively coupled to the programmableinformation-processing device to provide feedback control in order tocontrol the impedance of the first antenna element.

In some embodiments, the present invention provides a computer-readablemedium having instructions stored thereon for causing a suitablyprogrammed information processor to execute a method that includes:distributively power amplifying RF pulses within a bore of an MR magnetto obtain high-power RF pulses; coupling the high-power RF pulses to aplurality of antenna elements in the bore of the MR magnet; receiving anpreamplifying RF signals from the plurality of antenna elements in thebore of the MR magnet; and controlling the distributively poweramplifying and the preamplifying of the received RF signals. In someembodiments of the computer-readable medium, the method further includespower amplifying the RF pulses to a power of at least 1000 watts perantenna element. In some embodiments of the computer-readable medium,the method further includes controlling resistance, inductance andcapacitance (RLC) values of a circuit.

In some embodiments, the present invention provides an apparatus thatincludes: an MRI coil unit having a plurality of antenna elements,including a first antenna element and a second antenna element, whereinthe MRI coil unit is compatible for use in a bore of an MR magnet; and aplurality of power amplifiers, including a first power amplifier and asecond power amplifier, the plurality of power amplifiers located in theMRI coil unit, wherein the first power amplifier is configured, based ona control signal from a location remote from the plurality of antennaelements, to power amplify a first RF pulse to obtain a first high-powerRF pulse, wherein the first high-power RF pulse is coupled to at leastthe first antenna element but not to the second antenna element, andwherein the second power amplifier is configured to power amplify asecond RF pulse to obtain a second high-power RF pulse, wherein thesecond high-power RF pulse is coupled to at least the second antennaelement but not to the first antenna element, wherein the plurality ofpower amplifiers are configured for operation in the bore of the MRmagnet. In some embodiments of the apparatus, the first power amplifieris thermally coupled primarily to the first antenna element and thesecond power amplifier is thermally coupled primarily to the secondantenna element.

It is to be understood that the above description is intended to beillustrative, and not restrictive. Although numerous characteristics andadvantages of various embodiments as described herein have been setforth in the foregoing description, together with details of thestructure and function of various embodiments, many other embodimentsand changes to details will be apparent to those of skill in the artupon reviewing the above description. The scope of the invention shouldbe, therefore, determined with reference to the appended claims, alongwith the full scope of equivalents to which such claims are entitled. Inthe appended claims, the terms “including” and “in which” are used asthe plain-English equivalents of the respective terms “comprising” and“wherein,” respectively. Moreover, the terms “first,” “second,” and“third,” etc., are used merely as labels, and are not intended to imposenumerical requirements on their objects.

What is claimed is:
 1. A method comprising: providing an MRI coil havinga plurality of antenna elements, including a first antenna element and asecond antenna element; locating the MRI coil in a bore of an MR magnet;based on a control signal from a location remote from the plurality ofantenna elements, power amplifying a first RF pulse to obtain a firsthigh-power RF pulse and power amplifying a second RF pulse to obtain asecond high-power RF pulse; and coupling the first high-power RF pulseto at least the first antenna element but not to the second antennaelement and coupling the second high-power RF pulse to at least thesecond antenna element, wherein the power amplifying is performed in thebore of the MR magnet.
 2. The method of claim 1, further comprisingcoupling heat from the power amplifying the first RF pulse primarily tothe first antenna element, and coupling heat from the power amplifyingthe second RF pulse primarily to the second antenna element.
 3. Themethod of claim 1, wherein the first RF pulse has a power of less thanone watt and the first high-power pulse has a power of at least 100watts.
 4. The method of claim 1, wherein the first RF pulse has a powerof less than one watt and the first high-power pulse has a power of atleast 1000 watts.
 5. The method of claim 1, further comprisingelectrically controlling an impedance of the first antenna element tomatch an impedance of the power amplifying.
 6. The method of claim 1,further comprising using a programmable information-processing deviceoperatively coupled to control operation of the power amplifying in theMRI coil from a location at least one meter away from the MRI coil. 7.The method of claim 6, further comprising: electrically controlling animpedance of the first antenna element to match an impedance of thepower amplifying; and using a feedback signal operatively coupled to theprogrammable information-processing device to provide feedback controlin order to control the impedance of the first antenna element.
 8. Anon-transitory computer-readable medium having instructions storedthereon for causing a suitably programmed information processor toexecute a method that comprises: distributively power amplifying RFpulses within a bore of an MR magnet to obtain high-power RF pulses;coupling each of the high-power RF pulses to a proper subset of aplurality of antenna elements in the bore of the MR magnet; receivingand preamplifying RF signals from the plurality of antenna elements inthe bore of the MR magnet; and controlling the distributively poweramplifying and the preamplifying of the received RF signals.
 9. Thecomputer-readable medium of claim 8, wherein the medium further includesinstructions such that the method further includes power amplifying theRF pulses to a power of at least 1000 watts per antenna element.
 10. Thecomputer-readable medium of claim 8, wherein the medium further includesinstructions such that the method further includes controllingresistance, inductance and capacitance (RLC) values of a circuit. 11.The computer-readable medium of claim 8, wherein the medium furtherincludes instructions such that the method further includes: controllingoperation of the power amplifying in the MRI coil from a location atleast one meter away from the MRI coil.
 12. The computer-readable mediumof claim 8, wherein the medium further includes instructions such thatthe method further includes: electrically controlling an impedance ofeach one of the plurality of antenna elements to match an impedance of apower amplifier; and using a feedback signal to provide feedback controlin order to control the impedance of the plurality of antenna elements.13. An apparatus comprising: an MRI coil unit having a plurality ofantenna elements, including a first antenna element and a second antennaelement, wherein the MRI coil unit is compatible for use in a bore of anMR magnet; a plurality of power amplifiers, including a first poweramplifier and a second power amplifier, the plurality of poweramplifiers located in the MRI coil unit, wherein the first poweramplifier is configured, based on a control signal from a locationremote from the plurality of antenna elements, to power amplify a firstRF pulse to obtain a first high-power RF pulse, wherein the firsthigh-power RF pulse is coupled to at least the first antenna element butnot to the second antenna element, and wherein the second poweramplifier is configured to power amplify a second RF pulse to obtain asecond high-power RF pulse, wherein the second high-power RF pulse iscoupled to at least the second antenna element, wherein the plurality ofpower amplifiers are configured for operation in the bore of the MRmagnet.
 14. The apparatus of claim 13, wherein the first power amplifieris thermally coupled primarily to the first antenna element and thesecond power amplifier is thermally coupled primarily to the secondantenna element.
 15. The apparatus of claim 13, wherein the plurality ofpower amplifiers is thermally coupled to the plurality of antennaelements.
 16. The apparatus of claim 13, wherein the first poweramplifier amplifies the first RF pulse from a power of less than onewatt to a power of at least 100 watts.
 17. The apparatus of claim 13,wherein the first power amplifier amplifies the first RF pulse from apower of less than one watt to a power of at least 1000 watts.
 18. Theapparatus of claim 13, further comprising a controller operativelycoupled to the first antenna element and configured to electricallycontrol an impedance of the first antenna element to match an impedanceof the first power amplifier.
 19. The apparatus of claim 13, furthercomprising a programmable information-processing device operativelycoupled to control operation of the plurality of power amplifiers in theMRI coil from a location at least one meter away from the MRI coil. 20.The apparatus of claim 13, further comprising: a controller operativelycoupled to the first antenna element and configured to electricallyperform an impedance adjustment of the first antenna element to match animpedance of the first power amplifier; a programmableinformation-processing device operatively coupled the controller andconfigured to control operation the impedance adjustment, and to controloperation of the plurality of power amplifiers in the MRI coil from alocation at least one meter away from the MRI coil; and a feedbackcircuit that generates a feedback signal operatively coupled to theprogrammable information-processing device to provide feedback controlin order to control the impedance adjustment of the first antennaelement.